Incomplete stent apposition (ISA) or stent malapposition is the lack of contact between stent struts and the underlying arterial wall. ISA has been associated with significantly higher levels of thrombus deposition1 and is typically assessed by intravascular imaging techniques such as optical coherence tomography (OCT) and intravascular ultrasound (IVUS).2–4 These imaging modalities are useful to see whether or not malapposition occurs, albeit within the limit of detection of these modalities, but the resulting cross-sectional images do not allow a detailed analysis of the overall appositioning behaviour of the stent. For example, from these 2D images it is hard to investigate whether or not certain parts of a stent design are more vulnerable to malapposition. Recently, we have introduced a new approach to study the phenomenon of ISA based on finite element simulations.5 Such simulations are used during the development process of new devices as they allow the optimisation of a design without having to manufacture every intermediate design iteration.They have also proven to be a valuable tool to investigate and optimise interventional procedures such as bifurcation stenting.6–7 Standard results from these simulations are the stent and vessel deformations and the internal stresses and strains. Based on the predicted deformations, the strut–artery distance can be calculated over the complete stent length, giving additional insights into the 3D appositioning behaviour.
In this paper, we applied this virtual strut apposition assessment technique in the setting of bifurcation stenting, associated with a high degree of malapposition in certain cases. The strut–artery distances predicted by the simulations were compared with measurements based on OCT imaging following in vitro stent deployment.
Materials and Methods
Commercially available stents were deployed in a stenotic bifurcation model using a provisional approach. This was achieved virtually using finite element simulations and in vitro using silicone models, allowing for a comparison of the strut malapposition measured with both approaches. The diameters of the proximal main vessel, the distal main vessel and the side branch are 3.5 mm, 2.8 mm and 2.5 mm respectively, leading to a model in agreement with Finet’s and Murray’s law.8–9 The silicone models were built using rapid prototyping techniques (Objet Eden 350V printer, Objet GeometriesInc., Billerica, MA).
The stents used for this study were the bare metal Integrity stent(Medtronic, Minneapolis, MN) and Multi-Link 8 stent (Abbott Vascular,Santa Clara, CA). Stent sizes (3.0 mm x 18 mm) were taken according to the distal main vessel, following the recommendation of theEuropean Bifurcation Club.10
Stent Deployment and Postdilatation
Stents were placed over the side branch. Initial deployment pressure was chosen to achieve a balloon:artery ratio of 1.1:1 in the distal main branch. Effectively, 9 atm was used for the Integrity stent and 11 atm for the Multi-Link 8 stent. Postdilatation of the segment proximal to the side branch was performed using a 3.5 mm balloon that was inflated at 15 atm in the proximal main vessel to reach a balloon–artery ratio of 1.1:1at the proximal segment. This proximal optimisation technique (POT)improves the strut apposition in the proximal main vessel and is recommended in case of difficulty re-crossing into the side branch.11Final kissing inflation was not performed. The employed stenting procedure is depicted in Figure 1, as well as the virtual and silicone bifurcation model.
In Vitro Optical Coherence Tomography Imaging
Two samples of each stent were deployed at room temperature in the silicone models described above. The silicone models were submerged in a Ringer’s lactate solution during the complete stenting procedure. OCT (C7 Dragonfly™, St Jude Medical, St Paul, MN) was performed before and after stent deployment and after postdilating the proximal main vessel with a pullback speed of 10 mm/s. The resulting images were quantitatively analysed using dedicated software (QCU-CMS, Medis Medical Imaging Systems, Leiden, TheNetherlands). In particular, stent malappostion in the non-diseased proximal main vessel after initial stent deployment was quantified by averaging the individual strut–artery distances in five OCT images. OCT only accurately shows the endoluminal strut surface and, therefore,strut thickness (93 μm for the Integrity stent, 81 μm for the Multi-Link8 stent) was subtracted from the measured values. In addition, the stent area was determined at the location of maximal narrowing.
Finite Element Simulations
Stent models were generated starting from high-resolution micro-computed tomography (CT) images of the crimped stents5 and material properties were taken from O’Brien et al.12 Then the stents were combined with folded balloon models that led to a realistic compliance behaviour of the balloon-stent systems. This was verified by comparing the virtual compliance behaviour with the data reported by the stent manufacturers, showing that the maximum percentage difference in diameter was less than 1 % within the applied pressure range. The same accuracy in compliance behaviour was obtained for the post-dilation balloon model. The virtual stenting procedure was performed using the Abaqus/Explicit finite element solver (Dassault Systemes SIMULIA,Providence, RI). The virtually stented artery models were then imported in pyFormex (www.pyFormex.org) where the strut apposition measurements were performed, both after initial stent deployment and after post-dilation. The procedure allows automated quantification of the strut–artery distance in every node lying on the (outer) strut surface. For the calculation of the average strut–artery distance in the non-diseased part of the proximal main vessel, only the values in the nodes from the centreline of the outer stent surface were considered. For the Integrity stent, which has circular struts, the initial outermost point of the struts was considered.
Stent sizing according to the distal main vessel typically leads to malapposition in the proximal main vessel, which can be optimised by aproximal post-dilation as shown in Figure 2. Based on the simulation results, the post-dilation reduces the average strut–artery distance in the healthy proximal main vessel from 126 μm to 4 μm for the Integrity stent, and from 150 μm to 10 μm for the Multi-Link 8 stent.
The contour plots shown in Figure 3 are based on the simulations and illustrate the stent strut apposition of the different investigated stents before and after post-dilation. A blue colour corresponds with a minimal distance between the struts and the inner arterial wall and thus with a good apposition of the stent struts, whereas a red colour reflects a larger strut–artery distance. This figure illustrates again the impact of the post-dilation on strut apposition in the proximal stent segment. The red coloured region in the centre of the stent corresponds with the floating struts at the side branch ostium. The impact of post-dilation can also be assessed by quantifying the percentage of struts at a distance larger than 20 μm. Post-dilation reduces this percentage from 47 % to 8 % for the Integrity stent, and from 54 % to 16 % for the Multi-Link 8 stent.
The comparison of the simulation results and the OCT measurements is summarised in Table 1. For the Integrity stent, the simulation predicts an average malapposition (in the proximal main vessel) of 126 μm, while the analysis of the OCT images resulted in an average strut–artery distance of 117±14 μm. For the Multi-Link 8stent, this average distance is 150 μm and 174±7 μm for the simulation and the in vitro OCT measurements, respectively. In addition, Table 1 also contains the stent area at the location of maximal stenosis before and after post-dilation, based on both the simulations and the OCT analysis.
Stent malapposition is typically investigated by intravascular imaging modalities such as IVUS and OCT, the latter having a higher resolution(15 μm versus 150 μm), which may reveal malapposition in greater detail. Recently, a new approach has been introduced to study the phenomenon of ISA, based on finite element simulations.5 In the present study, both approaches were compared when stenting the main branch of a bifurcation using the same stenting procedure and bifurcation model during an in vitro and virtual bench test, and the obtained strut apposition results corresponded well. The small differences can be attributed to many factors, such as assumptions made for the finite element modelling, inaccuracies in the silicone models, limited resolution of the OCT images and small procedural differences (e.g. applied pressure).
The virtual strut apposition assessment may help to better understand and to minimise acute ISA as it gives additional information compared with traditional evaluation methods (IVUS and OCT). A first advantage is that the strut–artery distance can be quantified and visualised over the complete stent length, while currently used ISA measurements are typically based on IVUS and OCT cross-sectional images. This allows identification of the location of the malapposed struts with respect to the artery and plaque morphology. Furthermore, the impact of different stent designs can be investigated and the apposition behaviour of new stents could be optimised during the design phase. The detailed contour plots shown in Figure 3 reveal, for example, the occurrence of a small gap at the location of every U-turn in the bridging members of theMulti-Link 8 design. This gap seems to be caused by the strong circumferential curvature of this U-turn. The proposed virtual ISA measurement procedure could also be used to investigate and quantify the impact of different post-dilation strategies (e.g., balloon compliance,balloon pressure) and could provide additional insight in more complex bifurcation stenting techniques, where large strut malapposition frequently occurs.
Both the OCT measurement and the simulation results indicate that the Integrity stent struts are slightly closer to the vessel wall as compared with the Multi-Link 8 stent, both before and after post-dilation. The difference in strut thickness between the two stents partially explains this finding, but other factors are affecting this strut–artery distance, such as the expanded stent diameter at maximal balloon pressure, strut shape and stent recoil.
The in vitro and virtual deployments have been further compared by quantifying the stent area at the location of maximal stenosis. The obtained stent areas correspond well before post-dilation, but a considerable difference (1.24 mm2) can be observed after post-dilation of the Integrity stent. A different rotational position of the stent during the in vitro and virtual bench test could explain this discrepancy. There is, for example, a connection or weld between the struts located at the side branch ostium during the simulated case that limits the expansion of the struts into the side branch and thus the measured stent area (Figure 4).
The virtual stent apposition analysis has up to now only been used for research purposes, using simplified arterial models. It would of course be valuable to obtain this kind of highly detailed strut apposition measurement when treating real patients and there might be two alternative approaches to reach this goal: a first one could be based on advanced OCT image analysis and reconstruction. It should be feasible to create similar 3D contour plots of ISA over the complete stent length using 3D OCT reconstructions (see Figure 4). Such analysis would require robust and automatic strut and lumen detection methods.Alternatively, simulations based on pre-operative patient images (e.g. CT combined with IVUS13 or OCT to gain a higher resolution) could be used to study strut apposition using the same methodology as presented in this study. This approach, which is at least as ambitious as the first one,would allow very detailed strut apposition analysis (see Figure 3), but the predictive power of these simulations for real patient treatment first needs to be proven.
The assessment of strut apposition using computer simulations results in similar strut–artery distances when compared with measurements based on OCT-visualised in vitro stent deployments. Furthermore, it allows detailed three-dimensional visualisation of strut–artery distances over the complete stent length, providing useful insights into the phenomenon of stent strut malapposition. This approach could be applied to optimise devices and procedures.